EP3197381B1 - Laser lithotripsiesystem - Google Patents

Laser lithotripsiesystem Download PDF

Info

Publication number
EP3197381B1
EP3197381B1 EP15775348.4A EP15775348A EP3197381B1 EP 3197381 B1 EP3197381 B1 EP 3197381B1 EP 15775348 A EP15775348 A EP 15775348A EP 3197381 B1 EP3197381 B1 EP 3197381B1
Authority
EP
European Patent Office
Prior art keywords
fiber
laser
optical fiber
tip
terminating end
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Active
Application number
EP15775348.4A
Other languages
English (en)
French (fr)
Other versions
EP3197381A1 (de
Inventor
Jian James ZHANG
Rongwei Jason Xuan
Danop RAJABHANDHARAKS
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Boston Scientific Scimed Inc
Original Assignee
Scimed Life Systems Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Scimed Life Systems Inc filed Critical Scimed Life Systems Inc
Priority to EP24179752.1A priority Critical patent/EP4413938A3/de
Priority to EP20157020.7A priority patent/EP3673853B1/de
Publication of EP3197381A1 publication Critical patent/EP3197381A1/de
Application granted granted Critical
Publication of EP3197381B1 publication Critical patent/EP3197381B1/de
Active legal-status Critical Current
Anticipated expiration legal-status Critical

Links

Images

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
    • A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
    • A61B18/26—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor for producing a shock wave, e.g. laser lithotripsy
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
    • A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
    • A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
    • A61B2018/2255—Optical elements at the distal end of probe tips
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
    • A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
    • A61B2018/2255—Optical elements at the distal end of probe tips
    • A61B2018/2266—Optical elements at the distal end of probe tips with a lens, e.g. ball tipped
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
    • A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
    • A61B2018/2255—Optical elements at the distal end of probe tips
    • A61B2018/2272—Optical elements at the distal end of probe tips with reflective or refractive surfaces for deflecting the beam
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
    • A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
    • A61B2018/2255—Optical elements at the distal end of probe tips
    • A61B2018/2288—Optical elements at the distal end of probe tips the optical fibre cable having a curved distal end
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
    • A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
    • A61B18/26—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor for producing a shock wave, e.g. laser lithotripsy
    • A61B2018/263—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor for producing a shock wave, e.g. laser lithotripsy the conversion of laser energy into mechanical shockwaves taking place in a liquid

Definitions

  • Embodiments of the present invention generally relate to laser fibers for performing a medical laser treatment.
  • Medical lasers have been used in various practice areas, such as, for example, urology, neurology, otorhinolaryngology, general anesthetic ophthalmology, dentistry, gastroenterology, cardiology, gynecology, and thoracic and orthopedic procedures. Generally, these procedures require precisely controlled delivery of laser energy as part of the treatment protocol.
  • ESWL extracorporeal shock wave lithotripsy
  • laser laser lithotripsy
  • a holmium doped yttrium aluminium garnet (Ho:YAG) laser rod, or a thulium doped yttrium aluminium garnet (Tm:YAG) laser rod are used to produce laser energy having a wavelength of around 2000-2100 nm to break up stones of all types.
  • the laser energy is typically in the form of a train of laser pulses, each having long pulse widths, such as approximately a few hundred microseconds.
  • thermo-mechanical mechanism of action is in play for breaking up the stones, namely the laser energy superheats fluid in the vicinity of the stone, and creates a vaporization bubble.
  • the vaporization bubble then expands as a shockwave and destabilizes the stone, causing it to fragment.
  • document JP S61 193653 A describes disintegration of a concretion which is surrounded by a fluid, in particular disintegration of concretions in living organisms, by means of a light pulse guided via a light guide.
  • the light pulse emerging from the light guide is focused in such a way that its energy density exceeds the breakdown threshold of the fluid, and the resulting acoustic shock wave is directed at the concretion.
  • Document DE 37 27 003 A1 describes an application part for a rigid or flexible endoscope with a viewing channel and a working channel extending in parallel with the viewing channel.
  • the working channel has a guide and a defined stop for an insertable fibreoptic waveguide that can be coupled to a laser light source.
  • the working channel has an optical system for concentrating the laser light emerging from the fibreoptic waveguide onto a punctiform region. That part of the working channel which surrounds the punctiform region is designed as a shock wave reflector.
  • there is a rinsing channel whose outlet orifice is directed at least partially onto the light emergence area of the optical system.
  • Document WO 91/05332 A describes a method of transmitting extremely high light intensities through optical fiber systems for producing shock waves to destroy stones in the human body, wherein two or more consecutive pulses are transmitted through a light waveguide, the slope of the shock wave front being determined by the displacement in time of the individual pulses as well as device for the implementation of this method.
  • Document US 5 944 687 (A ) describes an optically activated transducer for generating acoustic vibrations in a biological medium.
  • the transducer is located at the end of a fiber optic which may be located within a catheter.
  • Energy for operating the transducer is provided optically by laser light transmitted through the fiber optic to the transducer.
  • Pulsed laser light is absorbed in the working fluid of the transducer to generate a thermal pressure and consequent adiabatic expansion of the transducer head such that it does work against the ambient medium.
  • the transducer returns to its original state by a process of thermal cooling. The motion of the transducer within the ambient medium couples acoustic energy into the medium.
  • an ultrasonic radiation field can be established locally in the medium.
  • This method of producing ultrasonic vibrations can be used in vivo for the treatment of stroke-related conditions in humans, particularly for dissolving thrombus.
  • the catheter may also incorporate anti-thrombolytic drug treatments as an adjunct therapy and it may be operated in conjunction with ultrasonic detection equipment for imaging and feedback control.
  • Document DE 38 36 337 A1 describes a method and a device for recording shock waves generated intracorporally as a result of a laser-induced break-through of a suitable matter in a rinsing medium for the purpose of crushing objects in organs, vessels or the like, by measuring the pressure of the reflected shock waves.
  • the laser fiber includes an optical fiber and a fiber tip.
  • the optical fiber includes a terminating end surface at a distal end.
  • the fiber tip is positioned at the distal end of the optical fiber and includes a transmissive portion and a spacer portion. Laser energy discharged from the terminating end surface of the optical fiber is transmitted through the transmissive portion.
  • the spacer portion defines a distal terminating end of the fiber tip that is spaced a predetermined distance from the terminating end surface of the optical fiber. The predetermined distance is set for shock wave generation for calculus destruction at the distal terminating end of the fiber tip.
  • Embodiments of the surgical laser system include a laser generator and the optical fiber formed in accordance with one or more embodiments.
  • the laser generator is configured to output laser energy that is optically coupled to a proximal end of the optical fiber.
  • the laser energy is transmitted through the optical fiber and is discharged through the terminating end surface of the optical fiber and the fiber tip.
  • the calculus is engaged with the terminating end of the fiber tip to position the terminating end surface of the optical fiber at the predetermined distance from the calculus.
  • Laser energy is transmitted through the optical fiber.
  • the laser energy is discharged through the terminating end surface of the optical fiber and the calculus is exposed to the laser energy while the calculus is maintained at the predetermined distance from the terminating end surface using the spacer portion.
  • the calculus is fragmented in response to the exposure to the laser energy.
  • Embodiments of the present invention generally relate to laser fibers for use in performing a medical laser treatment, such as laser lithotripsy, surgical laser systems utilizing such laser fibers, and methods of performing laser lithotripsy procedures using the laser fibers.
  • a medical laser treatment such as laser lithotripsy
  • surgical laser systems utilizing such laser fibers and methods of performing laser lithotripsy procedures using the laser fibers.
  • laser lithotripsy procedures using the laser fibers.
  • FIG. 1 is a schematic diagram of an exemplary surgical laser system 100, which includes a laser fiber 102 in accordance with one or more embodiments of the invention.
  • FIGS. 2-7 are simplified cross-sectional views of exemplary laser fibers 102 in accordance with embodiments of the invention.
  • FIG. 4 is a simplified cross-sectional view of a fiber tip of FIG. 4 taken generally along line 4-4.
  • the system 100 comprises a laser generator 104 that generates laser energy 106 and a waveguide 108 optically coupling the laser generator 104 to the laser fiber 102.
  • the laser fiber 102 either includes the waveguide 108 or is optically coupled to the waveguide 108.
  • the laser energy 106 is discharged from a distal end of the laser fiber 102, i.e., the end of the laser fiber 102 that is adjacent to the treatment site of a patient, and can be used to perform a desired medical laser procedure, such as tissue ablation, or urinary or kidney stone fragmentation.
  • the system 100 includes a probe 110 ( FIG. 1 ), in which at least a distal end of the laser fiber 102 is supported.
  • the laser generator 104 comprises one or more conventional laser sources, such as laser resonators, that produce the laser energy 106 having desired properties.
  • the system 100 produces the laser energy 106 in the form of a pulse train or continuous wave.
  • the laser generator 102 includes Q-switched laser rods to produce the laser energy 106, such as, for example, a holmium doped yttrium aluminium garnet (Ho:YAG) laser rod, a thulium doped yttrium aluminium garnet (Tm:YAG) laser rod, or other conventional laser rod suitable for producing the desired laser energy 106.
  • the laser energy 106 has a power of approximately 1-50W, a pulse repetition frequency of 1-2000Hz, and an energy level of 1mJ-5J. Laser energy 106 having other parameters may also be used.
  • the laser fiber 102 includes an optical fiber 112 and a fiber tip 114.
  • the optical fiber 112 includes a terminating end surface 116 at a distal end 118.
  • the fiber tip 114 includes a distal terminating end 120 that is spaced a predetermined distance 122 from the terminating end surface 116 of the optical fiber 112.
  • the fiber tip 114 operates to protect the distal end 118 of the optical fiber.
  • the fiber tip 114 can prevent or reduce damage to the distal end 118 of the optical fiber 112 that can occur during medical laser treatments due to contact between the distal end 118 of the optical fiber 112 and the targeted object for the laser energy 106, such as a calculus (i.e., kidney or bladder stone) 124 or tissue.
  • the fiber tip 114 forms a sealed cavity 125 around the terminating end surface 116 of the optical fiber, as shown in FIG. 2 .
  • the predetermined distance or spacing 122 is generally set to alleviate/control damage to the distal end 118 of the optical fiber 112, manipulate (focus or diffuse) a shock wave generated during laser lithotripsy, and improve ablation efficiency.
  • FIG. 8 shows photos of laser lithotripsy operations using a Ho:YAG laser, and a Tm:YAG laser that show a bubble formation process and oscillations during the laser-stone interaction.
  • FIG. 9 is a chart illustrating a relationship between an ablation volume and the spacing 122 between the terminating end surface 116 or fiber tip of the optical fiber 112 and the calculus 124 for a Ho:YAG laser (1.0 J, 10Hz, ⁇ 109 ⁇ s) and a Tm:YAG laser (40mJ, 250Hz, 190ns).
  • the chart illustrates that the ablation efficiency for the Ho:YAG laser is higher when the spacing 122 is 0.5mm as compared to when the surface 116 of the optical fiber 112 is in contact with the calculus 124.
  • the chart shows that the ablation efficiency of the Tm:YAG laser is similar over the spacing 122 of 0-0.5mm.
  • the spacing 122 between the surface 116 of the optical fiber 112 and the targeted object (e.g., calculus 124) provided by the fiber tip 114 can allow for efficient ablation of the targeted object while protecting the optical fiber 122.
  • the distance 122 is approximately 0.1-4 mm. In some embodiments, the distance 122 is 0.1mm-1mm.
  • the fiber tip 114 is attached to the laser fiber 112, as shown in FIGS. 2 and 5-7 . In some embodiments, this involves attaching the fiber tip 114 to a core of the optical fiber 112, cladding of the optical fiber 112, and/or a jacket surrounding the cladding and core of the optical fiber 112, which are not shown in order to simplify the illustrations. In some embodiments, the fiber tip 114 is removably attached to the optical fiber 112. In some embodiments, the fiber tip 114 may be attached to the distal end 118 of the optical fiber 112 by hand, and may also be detached from the optical fiber 112 by hand.
  • the optical fiber 112 may be supported within a fiber support 126, as shown in FIG. 3 .
  • the fiber support 126 may be a tubular member through which the optical fiber 112 is inserted.
  • the fiber tip 114 attaches directly to the fiber support 126 rather than the optical fiber 112, as shown in FIG. 3 .
  • the fiber tip 114 is removably attachable to the fiber support 126.
  • the attachment and removal of the fiber tip 114 from the fiber support 126 may be performed by hand.
  • the fiber tip 114 includes a sleeve portion 128 that facilitates attachment of the fiber tip 114 to either the optical fiber 112 ( FIG. 2 ) or a fiber support 126 ( FIG. 3 ).
  • at least a proximal end 130 of the sleeve portion 128 forms a socket that is configured to receive the distal end 118 of the optical fiber 112 ( FIG. 2 ) or a distal end 132 of the fiber support 126 ( FIG. 3 ).
  • the sleeve portion 128 includes a shoulder 134 that is configured to engage the terminating end surface 116 of the optical fiber 112 ( FIG. 2 ) or an end surface 136 of the fiber support 126 ( FIG. 3 ) to position the terminating end 120 of the fiber tip 114 at the desired distance 122 from the terminating end surface 116 of the optical fiber 112.
  • the fiber tip 114 includes a transmissive portion 140, through which the laser energy 106 discharged from the terminating end surface 116 of the optical fiber 112 is transmitted. In some embodiments, the laser energy 106 is discharged through the transmissive portion 140 along a longitudinal axis of the optical fiber 112.
  • the fiber tip 114 includes a spacer portion 142 that defines the distal terminating end 120 of the fiber tip 114.
  • the transmissive portion 140 includes the spacer portion 142, as shown in FIGS. 2 , 3 , 6 and 7 .
  • the spacer portion 142 extends distally from the transmissive portion 140, as shown in FIG. 5 .
  • the distal terminating end 120 of the spacer portion 142 is annular, as shown in FIG. 5 .
  • the distally extending spacer portion 142 may comprise one or more projections.
  • the sleeve portion 128 supports the transmissive portion 140 and the spacer portion 142. In some embodiments, the sleeve portion 128 surrounds the distal end 118 of the optical fiber 112. In some embodiments, the sleeve portion 128, the transmissive portion 140, and the spacer portion 142 are formed as a single component, as shown in FIG. 7 .
  • components of the fiber tip 114 such as the transmissive portion 140, the spacer portion 142, and/or the sleeve portion 128, are formed of sapphire or hard glass.
  • the transmissive portion 140 includes one or more lenses that assist in focusing or diffusing the laser energy 106 that is directed to the targeted object, such as a calculus 124.
  • a lens 144 is located at the distal end of the transmissive portion 140, as shown in phantom in FIG. 2 .
  • the transmissive portion 140 includes a lens 146 located at a proximal end of the transmissive portion 140, as shown in phantom in FIG. 2 .
  • the distal terminating end 120 of the fiber tip 114 includes a convex surface 150, as shown in FIGS. 6 and 7 .
  • the surface 150 may operate as the distal lens 144 ( FIG. 2 ).
  • the convex surface 150 operates to diffuse the shock wave that occurs during laser lithotripsy to reduce retropulsion of the calculus or stone 124.
  • Another embodiment of the invention is directed to a method of fragmenting a calculus using a laser fiber 102 formed in accordance with one or more embodiments of the present invention.
  • the calculus 124 is engaged with the terminating end 120 of the fiber tip 114 to position the terminating end surface 116 of the optical fiber 112 at the predetermined distance 122 from the calculus, as shown in FIGS. 2 , 3 and 5 .
  • Laser energy 106 is then transmitted through the optical fiber 112 and discharged through the terminating end surface 116.
  • the calculus or stone 124 is exposed to the laser energy 106 while the calculus is at the predetermined distance 122 from the terminating end surface 116.
  • the calculus is then fragmented responsive to the exposure of the calculus to the laser energy 106 and the shock wave generated thereby.
  • fiber tips 114 can be detachably mounted to the laser fiber 102, the fiber tips 114 can be designed for specific procedures, types of calculi, etc. Accordingly, a single laser fiber can be used with different fiber tips 114 to perform multiple different types of procedures more efficiently and with better outcomes.

Landscapes

  • Health & Medical Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Surgery (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Optics & Photonics (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Molecular Biology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Electromagnetism (AREA)
  • Medical Informatics (AREA)
  • Otolaryngology (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Laser Surgery Devices (AREA)
  • Optical Couplings Of Light Guides (AREA)
  • Radiation-Therapy Devices (AREA)

Claims (13)

  1. Laserfaser (102) zum Durchführen einer Laserlithotripsie, umfassend:
    eine Lichtleitfaser (112) mit einem distalen Ende (118) und einer Anschlussende-Oberfläche (116) am distalen Ende (118); und
    eine Faserspitze (114) am distalen Ende (118) der Lichtleitfaser (112), wobei die Faserspitze (114) einen Übertragungsabschnitt (140), durch den von der Anschlussende-Oberfläche (116) der Lichtleitfaser (112) abgegebene Laserenergie übertragen wird, und einen Beabstandungsabschnitt (142), der ein distales Anschlussende (120) der Faserspitze (114) definiert, das in einem vorgegebenen Abstand (122) von der Anschlussende-Oberfläche (116) der Lichtleitfaser (112) beabstandet ist, beinhaltet;
    wobei der vorgegebene Abstand (122) zur Stoßwellenerzeugung für die Steinbeseitigung am distalen Anschlussende (120) der Faserspitze (114) eingestellt ist,
    wobei der vorgegebene Abstand (122) zwischen 0,1 mm und 4 mm liegt,
    wobei die Faserspitze (114) einen abgedichteten Hohlraum (125) um die Anschlussende-Oberfläche (116) der Lichtleitfaser (112) bildet.
  2. Laserfaser (102) nach Anspruch 1, wobei die Faserspitze (114) am distalen Ende (118) der Lichtleitfaser (112) befestigt ist.
  3. Laserfaser (102) nach Anspruch 2, wobei die Faserspitze (114) am distalen Ende (118) der Lichtleitfaser (112) abnehmbar befestigt ist.
  4. Laserfaser (102) nach Anspruch 1, wobei die Lichtleitfaser (112) in einer Faserhalterung (126) enthalten ist und die Faserspitze (114) an der Faserhalterung (126) befestigt ist.
  5. Laserfaser (102) nach Anspruch 4, wobei die Faserspitze (114) an der Faserhalterung (126) abnehmbar befestigt ist.
  6. Laserfaser (102) nach einem der Ansprüche 1 bis 5, wobei der Übertragungsabschnitt (140) den Beabstandungsabschnitt (142) aufweist.
  7. Laserfaser (102) nach einem der Ansprüche 1 bis 5, wobei sich der Beabstandungsabschnitt (142) distal von dem Übertragungsabschnitt (140) erstreckt.
  8. Laserfaser (102) nach einem der Ansprüche 1 bis 7, wobei die Faserspitze (114) einen Hülsenabschnitt (128) mit einem proximalen Ende (130), das das distale Ende (118) der Lichtleitfaser (112) umschließt und den Übertragungsabschnitt (140) und den Beabstandungsabschnitt (142) trägt, umfasst.
  9. Laserfaser (102) nach einem der Ansprüche 1 bis 8, wobei der Übertragungsabschnitt (140) eine Linse (144, 146) umfasst, die von der Anschlussende-Oberfläche (116) der Lichtleitfaser (112) abgegebene Laserenergie bündelt.
  10. Laserfaser (102) nach Anspruch 9, wobei die Linse (146) an einem proximalen Ende des Übertragungsabschnitts (140) positioniert ist.
  11. Laserfaser (102) nach Anspruch 9, wobei die Linse (144) an einem distalen Ende des Übertragungsabschnitts (140) positioniert ist.
  12. Laserfaser (102) nach einem der Ansprüche 1 bis 11, wobei das distale Anschlussende (120) der Faserspitze (114) eine konvexe Oberfläche aufweist.
  13. Chirurgisches Lasersystem, umfassend eine Laserfaser (102) nach einem der Ansprüche 1 bis 12 und einen Lasergenerator (104), der eingerichtet ist, um Laserenergie auszugeben, die mit einem proximalen Ende der Lichtleitfaser (112) optisch gekoppelt ist, wobei die Laserenergie durch die Lichtleitfaser (112) übertragen wird und durch die Anschlussende-Oberfläche (116) der Lichtleitfaser (112) und die Faserspitze (114) abgegeben wird.
EP15775348.4A 2014-09-24 2015-09-23 Laser lithotripsiesystem Active EP3197381B1 (de)

Priority Applications (2)

Application Number Priority Date Filing Date Title
EP24179752.1A EP4413938A3 (de) 2014-09-24 2015-09-23 Laserlithotripsiesystem
EP20157020.7A EP3673853B1 (de) 2014-09-24 2015-09-23 Laser lithotripsiesystem

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US201462054582P 2014-09-24 2014-09-24
PCT/US2015/051687 WO2016049160A1 (en) 2014-09-24 2015-09-23 Laser lithotripsy system

Related Child Applications (3)

Application Number Title Priority Date Filing Date
EP20157020.7A Division EP3673853B1 (de) 2014-09-24 2015-09-23 Laser lithotripsiesystem
EP20157020.7A Division-Into EP3673853B1 (de) 2014-09-24 2015-09-23 Laser lithotripsiesystem
EP24179752.1A Division EP4413938A3 (de) 2014-09-24 2015-09-23 Laserlithotripsiesystem

Publications (2)

Publication Number Publication Date
EP3197381A1 EP3197381A1 (de) 2017-08-02
EP3197381B1 true EP3197381B1 (de) 2020-03-25

Family

ID=54252430

Family Applications (3)

Application Number Title Priority Date Filing Date
EP24179752.1A Pending EP4413938A3 (de) 2014-09-24 2015-09-23 Laserlithotripsiesystem
EP15775348.4A Active EP3197381B1 (de) 2014-09-24 2015-09-23 Laser lithotripsiesystem
EP20157020.7A Active EP3673853B1 (de) 2014-09-24 2015-09-23 Laser lithotripsiesystem

Family Applications Before (1)

Application Number Title Priority Date Filing Date
EP24179752.1A Pending EP4413938A3 (de) 2014-09-24 2015-09-23 Laserlithotripsiesystem

Family Applications After (1)

Application Number Title Priority Date Filing Date
EP20157020.7A Active EP3673853B1 (de) 2014-09-24 2015-09-23 Laser lithotripsiesystem

Country Status (4)

Country Link
US (1) US12303193B2 (de)
EP (3) EP4413938A3 (de)
CN (1) CN106604690A (de)
WO (1) WO2016049160A1 (de)

Families Citing this family (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
ES2778924T3 (es) 2016-05-18 2020-08-12 Gyrus Acmi Inc Aparato para litotricia láser
US10405923B2 (en) 2016-08-12 2019-09-10 Boston Scientific Scimed, Inc. Systems, devices, and related methods for laser lithotripsy
US12446961B2 (en) 2020-02-10 2025-10-21 Bolt Medical, Inc. System and method for pressure monitoring within a catheter system
US20240130788A1 (en) * 2022-02-04 2024-04-25 Gyrus Acmi, Inc. D/B/A Olympus Surgical Technologies America Medical devices with protected light conductors

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS61193653A (ja) * 1985-02-22 1986-08-28 メツセルシユミツト‐ベルコウ‐ブローム・ゲゼルシヤフト・ミト・ベシユレンクテル・ハフツング 固い物体を破砕するための方法および装置
DE3727003A1 (de) * 1986-08-13 1988-02-25 Messerschmitt Boelkow Blohm Applikationsteil fuer ein starres oder flexibles endoskop
DE3836337A1 (de) * 1988-10-25 1990-04-26 Meessen Stephan Dr B Verfahren und vorrichtung zum erfassen von intrakorporal erzeugten laserinduzierten stosswellen
WO1991005332A1 (de) * 1989-10-07 1991-04-18 Laser-Medizin-Zentrum Gmbh Berlin Verfahren und vorrichtung zur erzeugung von laserinduzierten stosswellen
US5944687A (en) * 1996-04-24 1999-08-31 The Regents Of The University Of California Opto-acoustic transducer for medical applications

Family Cites Families (99)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3467098A (en) 1967-03-24 1969-09-16 Becton Dickinson Co Flexible conduit for laser surgery
US4204743A (en) * 1976-06-21 1980-05-27 U.S. Philips Corporation Connector for coupling optical fibers to an emitter or receiver of luminous energy
US4273109A (en) 1976-07-06 1981-06-16 Cavitron Corporation Fiber optic light delivery apparatus and medical instrument utilizing same
US4817601A (en) * 1985-03-06 1989-04-04 C. R. Bard, Inc. Catheter system for controlled removal by radiant energy of biological obstructions
US5167686A (en) * 1985-03-06 1992-12-01 C. R. Bard, Inc. Catheter system for controlled removal by radiant energy of biological obstructions
US4718417A (en) 1985-03-22 1988-01-12 Massachusetts Institute Of Technology Visible fluorescence spectral diagnostic for laser angiosurgery
US5693043A (en) * 1985-03-22 1997-12-02 Massachusetts Institute Of Technology Catheter for laser angiosurgery
US4850351A (en) * 1985-05-22 1989-07-25 C. R. Bard, Inc. Wire guided laser catheter
US4917084A (en) * 1985-07-31 1990-04-17 C. R. Bard, Inc. Infrared laser catheter system
DE3686621T2 (de) * 1985-07-31 1993-02-25 Bard Inc C R Infrarot laser-kathetergeraet.
US4707073A (en) 1985-09-04 1987-11-17 Raytheon Company Fiber optic beam delivery system for high-power laser
US4732449A (en) 1985-10-25 1988-03-22 G & H Technology Beam splitter
US4695697A (en) 1985-12-13 1987-09-22 Gv Medical, Inc. Fiber tip monitoring and protection assembly
US4865029A (en) 1986-04-24 1989-09-12 Eye Research Institute Of Retina Foundation Endophotocoagulation probe
US4838246A (en) 1986-08-13 1989-06-13 Messerschmitt-Bolkow-Blohm Gmbh Application part for an endoscope
EP0268019A1 (de) 1986-11-13 1988-05-25 Messerschmitt-Bölkow-Blohm Gesellschaft mit beschränkter Haftung Vorrichtung zur Zertrümmerung eines von einem Fluid umgebenen festen Körpers
US4867136A (en) 1987-04-23 1989-09-19 Olympus Optical Co., Ltd. Endoscope apparatus
US5112328A (en) 1988-01-25 1992-05-12 Refractive Laser Research & Development Program, Ltd. Method and apparatus for laser surgery
DE3842916C1 (de) 1988-12-21 1990-02-01 Messerschmitt-Boelkow-Blohm Gmbh, 8012 Ottobrunn, De
US5425735A (en) 1989-02-22 1995-06-20 Psi Medical Products, Inc. Shielded tip catheter for lithotripsy
US5019040A (en) 1989-08-31 1991-05-28 Koshin Sangyo Kabushiki Kaisha Catheter
ES2099100T3 (es) 1989-10-25 1997-05-16 Jack Murray Dodick Instrumento quirurgico con transductor de la potencia de entrada.
US5257989A (en) 1990-02-07 1993-11-02 Coherent, Inc. Contact laser delivery probe
US5304171A (en) 1990-10-18 1994-04-19 Gregory Kenton W Catheter devices and methods for delivering
US5093877A (en) 1990-10-30 1992-03-03 Advanced Cardiovascular Systems Optical fiber lasing apparatus lens
US6110167A (en) * 1990-10-31 2000-08-29 Premier Laser Systems, Inc. Contact tip for laser surgery
US5269777A (en) * 1990-11-01 1993-12-14 Pdt Systems, Inc. Diffusion tip for optical fibers
US5224942A (en) 1992-01-27 1993-07-06 Alcon Surgical, Inc. Surgical method and apparatus utilizing laser energy for removing body tissue
ATE211008T1 (de) * 1992-04-10 2002-01-15 Surgilight Inc Gerät zur durchführung von augenchirurgie
US5291570A (en) 1992-09-09 1994-03-01 Hobart Laser Products, Inc. High power laser - optical fiber connection system
US5342355A (en) * 1992-10-19 1994-08-30 Laser Centers Of America Energy delivering cap element for end of optic fiber conveying laser energy
US5553629A (en) 1993-03-11 1996-09-10 The United States Of America As Represented By The Secretary Of The Air Force Portable medical laser pack system
FR2709763B1 (fr) 1993-09-08 1995-10-13 Commissariat Energie Atomique Dispositif de traitement d'un matériau, à tête photo-ionique miniaturisée.
US5526455A (en) 1993-09-17 1996-06-11 Sumitomo Electric Industries, Ltd. Connector including opposing lens surfaces, side surfaces, and contact surfaces for coupling optical devices
JP3167844B2 (ja) 1993-10-08 2001-05-21 テルモ株式会社 固体レーザ装置
US5496309A (en) * 1994-05-06 1996-03-05 Trimedyne, Inc. Catheter device utilizing a laser beam laterally directed by a high index prism in a liquid medium
US5599341A (en) 1994-06-15 1997-02-04 Keravision, Inc. Laser surgical procedure and device for treatment of the cornea
US5562657A (en) * 1994-09-19 1996-10-08 Griffin; Stephen E. Side fire laser catheter method and apparatus
US5738676A (en) 1995-01-03 1998-04-14 Hammer; Daniel X. Laser surgical probe for use in intraocular surgery
CA2146737C (en) 1995-04-10 2001-08-14 Yihao Cheng Integrated optical isolator
US5921981A (en) 1995-11-09 1999-07-13 Alcon Laboratories, Inc. Multi-spot laser surgery
US5680237A (en) 1995-11-16 1997-10-21 Jds Fitel Inc. Graded index lens system and method for coupling light
US5815623A (en) * 1996-01-18 1998-09-29 Methode Electronics, Inc. Optical package with alignment means and method of assembling an optical package
US5840075A (en) 1996-08-23 1998-11-24 Eclipse Surgical Technologies, Inc. Dual laser device for transmyocardial revascularization procedures
AU7568698A (en) 1997-05-15 1998-12-08 General Hospital Corporation, The Method and apparatus for dermatology treatment
US6393179B1 (en) 1997-07-18 2002-05-21 Jds Fitel Inc. Optical coupling system
US6157485A (en) 1997-07-18 2000-12-05 Cheng; Yihao Lens arrangement for enhancing the coupling of light shifted by an optical element
US6142630A (en) 1998-05-08 2000-11-07 Koester; Charles J. Variable focus lens system such as for examination or treatment of transparent or semi-transparent materials such as ocular tissue
US6175673B1 (en) 1998-10-29 2001-01-16 Jds Fitel Inc. Lensed sleeve
US6203537B1 (en) * 1999-02-04 2001-03-20 Sorin Adrian Laser-driven acoustic ablation catheter
US6484052B1 (en) 1999-03-30 2002-11-19 The Regents Of The University Of California Optically generated ultrasound for enhanced drug delivery
DE60043546D1 (de) 1999-07-26 2010-01-28 Labosphere Inst Linse, lichtemittierender körper, beleuchtungskörper und optisches informationssystem
US6219481B1 (en) 1999-08-05 2001-04-17 Jds Fitel Inc. Optical filter
US6556747B2 (en) 2001-02-09 2003-04-29 Lightmatrix Technologies, Inc. Chemical mill method and structure formed thereby
US6748137B2 (en) 2001-04-30 2004-06-08 Jds Uniphase Corporation Lensed optical fiber
US20020186742A1 (en) 2001-05-03 2002-12-12 Flint Graham W. Single mode autocoupled resonator for telecommunications
GB0111363D0 (en) 2001-05-09 2001-07-04 Point Source Ltd Optical component
US6692431B2 (en) 2001-09-07 2004-02-17 Smith & Nephew, Inc. Endoscopic system with a solid-state light source
US10595710B2 (en) 2001-10-19 2020-03-24 Visionscope Technologies Llc Portable imaging system employing a miniature endoscope
US8038602B2 (en) 2001-10-19 2011-10-18 Visionscope Llc Portable imaging system employing a miniature endoscope
US6863651B2 (en) 2001-10-19 2005-03-08 Visionscope, Llc Miniature endoscope with imaging fiber system
US6960307B2 (en) 2002-01-18 2005-11-01 Leclair Mark L Method and apparatus for the controlled formation of cavitation bubbles
US20040004055A1 (en) 2002-01-18 2004-01-08 Barros Emanuel F. Method and apparatus for the controlled formation of cavitation bubbles
US20060200113A1 (en) 2002-03-07 2006-09-07 David Haffner Liquid jet for glaucoma treatment
EP2134282B1 (de) * 2002-07-10 2019-05-22 AngioDynamics, Inc. Vorrichtung zur endovaskulären behandlung zum verschluss eines blutgefässes
US6945674B2 (en) 2002-07-16 2005-09-20 Ccs, Inc. Light irradiating unit
US20040052475A1 (en) * 2002-09-18 2004-03-18 E-Pin Optical Industry Co., Ltd. Fiber collimator and method of manufacturing the same
US20040097791A1 (en) 2002-11-13 2004-05-20 Olympus Corporation Endoscope
JP2005013708A (ja) 2003-05-30 2005-01-20 Olympus Corp 内視鏡及びその組立方法
DE10342016A1 (de) * 2003-09-11 2005-04-14 Siemens Ag Lithotripsie-Einrichtung
US20050113814A1 (en) * 2003-11-24 2005-05-26 Loeb Marvin P. Apparatus and method for limiting the re-use of fiber optic, laser energy delivery devices
WO2006095490A1 (ja) 2005-03-08 2006-09-14 Olympus Medical Systems Corp. 内視鏡、光学部材、内視鏡の製造方法
US20070027443A1 (en) * 2005-06-29 2007-02-01 Ondine International, Ltd. Hand piece for the delivery of light and system employing the hand piece
US20080108867A1 (en) 2005-12-22 2008-05-08 Gan Zhou Devices and Methods for Ultrasonic Imaging and Ablation
JP2007193006A (ja) * 2006-01-18 2007-08-02 Nippon Electric Glass Co Ltd 光通信用光学部品
US20070195548A1 (en) 2006-02-17 2007-08-23 Bwt Property, Inc. Light Emitting Panel for Medical Applications
EP1903361B1 (de) 2006-09-22 2020-04-01 Nippon Electric Glass Co., Ltd. Optisches Element und lichtemittierende Vorrichtung unter Verwendung desselben
JP5366575B2 (ja) 2008-05-08 2013-12-11 Ｈｏｙａ株式会社 複数機種の内視鏡
US9289262B2 (en) 2008-05-19 2016-03-22 Boston Scientific Scimed, Inc. Dielectric coatings for laser fiber and related methods
US8679103B2 (en) * 2008-12-22 2014-03-25 Valam Corporation Two step mammalian biofilm treatment processes and systems
WO2010075364A1 (en) * 2008-12-22 2010-07-01 Ams Research Corporation Sapphire-based delivery tip for optic fiber
US8109676B2 (en) 2009-06-12 2012-02-07 Applied Micro Circuits Corporation Fiber optic cable with high interface mismatch tolerance
JP4866961B2 (ja) 2010-04-16 2012-02-01 三菱鉛筆株式会社 光コリメータ及びこれを用いた光コネクタ、並びに、光コリメータ用保持部材
US9429717B2 (en) 2010-06-29 2016-08-30 Fujikura Ltd. Ferrule and ferrule with optical fiber
JP5435739B2 (ja) 2010-10-19 2014-03-05 国立大学法人東北大学 光ファイバーおよびそれを用いた水中衝撃波発生装置
CN102370520B (zh) * 2011-11-03 2013-09-18 温海涛 一种激光碎石固定钳
US8571364B2 (en) 2011-11-09 2013-10-29 Alcon Research, Ltd. Multi-spot laser probe with faceted optical element
US8861900B2 (en) 2012-02-23 2014-10-14 Corning Incorporated Probe optical assemblies and probes for optical coherence tomography
US8967885B2 (en) 2012-02-23 2015-03-03 Corning Incorporated Stub lens assemblies for use in optical coherence tomography systems
US9588302B2 (en) 2012-06-01 2017-03-07 Te Connectivity Corporation Expanded-beam connector with molded lens
US8711336B1 (en) 2012-11-01 2014-04-29 National Security Technologies, Llc Multipoint photonic doppler velocimetry using optical lens elements
US20160184022A1 (en) 2013-03-13 2016-06-30 The Spectranetics Corporation Laser-induced pressure wave emitting catheter sheath
US20140288369A1 (en) 2013-03-15 2014-09-25 Olive Medical Corporation Mechanical image rotation for rigidly coupled image sensor and endoscope
EP3037031A4 (de) 2013-12-18 2017-05-17 Olympus Corporation Endoskop und endoskopsystem
EP3097443B1 (de) 2014-01-22 2019-06-26 The Regents of the University of Colorado, a body corporate Optische bildgebungsvorrichtungen und linsenelemente mit variablem fokus sowie verfahren zur verwendung davon
US9645325B2 (en) 2015-05-01 2017-05-09 Corning Optical Communications LLC Expanded-beam ferrule with high coupling efficiency for optical interface devices
US9829698B2 (en) 2015-08-31 2017-11-28 Panasonic Corporation Endoscope
US9838576B2 (en) 2015-08-31 2017-12-05 Panasonic Corporation Endoscope
US10905322B2 (en) 2019-03-26 2021-02-02 John L. Bala Bala Laparoscope System

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS61193653A (ja) * 1985-02-22 1986-08-28 メツセルシユミツト‐ベルコウ‐ブローム・ゲゼルシヤフト・ミト・ベシユレンクテル・ハフツング 固い物体を破砕するための方法および装置
DE3727003A1 (de) * 1986-08-13 1988-02-25 Messerschmitt Boelkow Blohm Applikationsteil fuer ein starres oder flexibles endoskop
DE3836337A1 (de) * 1988-10-25 1990-04-26 Meessen Stephan Dr B Verfahren und vorrichtung zum erfassen von intrakorporal erzeugten laserinduzierten stosswellen
WO1991005332A1 (de) * 1989-10-07 1991-04-18 Laser-Medizin-Zentrum Gmbh Berlin Verfahren und vorrichtung zur erzeugung von laserinduzierten stosswellen
US5944687A (en) * 1996-04-24 1999-08-31 The Regents Of The University Of California Opto-acoustic transducer for medical applications

Also Published As

Publication number Publication date
US12303193B2 (en) 2025-05-20
EP3197381A1 (de) 2017-08-02
CN106604690A (zh) 2017-04-26
EP4413938A3 (de) 2024-09-18
EP3673853B1 (de) 2024-06-12
EP4413938A2 (de) 2024-08-14
WO2016049160A1 (en) 2016-03-31
US20220370130A1 (en) 2022-11-24
EP3673853A1 (de) 2020-07-01

Similar Documents

Publication Publication Date Title
US11439465B2 (en) Surgical laser systems and laser lithotripsy techniques
EP0959782B1 (de) Optoakustische thrombolyse
US5059200A (en) Laser lithotripsy
US8409176B2 (en) Method and device for laser lithotripsy
US12303193B2 (en) Surgical laser systems and laser lithotripsy techniques
KR101529367B1 (ko) 레이저 유발 증기/플라스마 매개 의학적 처치방법 및 장치
JP3113274B2 (ja) 入力パワー変換器を有す手術用装置
US11648150B2 (en) Laser apparatus for treatment of a cataractous lens
US6491685B2 (en) Laser and acoustic lens for lithotripsy
US20020045890A1 (en) Opto-acoustic thrombolysis
US5151098A (en) Apparatus for controlled tissue ablation
US4887600A (en) Use of lasers to break down objects
Grocela et al. Intracorporeal lithotripsy: instrumentation and development
JP2002537017A (ja) 吸引を用いるレーザー砕石術デバイス
US20140336626A1 (en) Medical assembly using short pulse fiber laser
WO1991010403A1 (en) Method and apparatus for fragmentation of hard substances
US7690382B2 (en) System and method for salivary stones removal and joint arthroscopy
EP0220304B1 (de) Laser zur zerstörung von steinen im menschlichen körper
Hofmann et al. First clinical experience with a Q-switched neodymium: YAG laser for urinary calculi
US5135534A (en) Laser lithotripsy
Celliers et al. Opto-acoustic thrombolysis
Qiu et al. Ho: YAG laser lithotripsy

Legal Events

Date Code Title Description
STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: THE INTERNATIONAL PUBLICATION HAS BEEN MADE

PUAI Public reference made under article 153(3) epc to a published international application that has entered the european phase

Free format text: ORIGINAL CODE: 0009012

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: REQUEST FOR EXAMINATION WAS MADE

17P Request for examination filed

Effective date: 20170420

AK Designated contracting states

Kind code of ref document: A1

Designated state(s): AL AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO RS SE SI SK SM TR

AX Request for extension of the european patent

Extension state: BA ME

DAV Request for validation of the european patent (deleted)
DAX Request for extension of the european patent (deleted)
STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: EXAMINATION IS IN PROGRESS

17Q First examination report despatched

Effective date: 20180515

GRAP Despatch of communication of intention to grant a patent

Free format text: ORIGINAL CODE: EPIDOSNIGR1

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: GRANT OF PATENT IS INTENDED

INTG Intention to grant announced

Effective date: 20191014

GRAS Grant fee paid

Free format text: ORIGINAL CODE: EPIDOSNIGR3

GRAA (expected) grant

Free format text: ORIGINAL CODE: 0009210

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: THE PATENT HAS BEEN GRANTED

AK Designated contracting states

Kind code of ref document: B1

Designated state(s): AL AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO RS SE SI SK SM TR

REG Reference to a national code

Ref country code: GB

Ref legal event code: FG4D

REG Reference to a national code

Ref country code: DE

Ref legal event code: R096

Ref document number: 602015049438

Country of ref document: DE

REG Reference to a national code

Ref country code: AT

Ref legal event code: REF

Ref document number: 1247672

Country of ref document: AT

Kind code of ref document: T

Effective date: 20200415

Ref country code: IE

Ref legal event code: FG4D

REG Reference to a national code

Ref country code: NL

Ref legal event code: FP

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: RS

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

Ref country code: FI

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

Ref country code: NO

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200625

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: SE

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

Ref country code: LV

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

Ref country code: BG

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200625

Ref country code: GR

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200626

Ref country code: HR

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

REG Reference to a national code

Ref country code: LT

Ref legal event code: MG4D

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: SK

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

Ref country code: SM

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

Ref country code: IS

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200725

Ref country code: PT

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200818

Ref country code: EE

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

Ref country code: LT

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

Ref country code: CZ

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

Ref country code: RO

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

REG Reference to a national code

Ref country code: AT

Ref legal event code: MK05

Ref document number: 1247672

Country of ref document: AT

Kind code of ref document: T

Effective date: 20200325

REG Reference to a national code

Ref country code: DE

Ref legal event code: R097

Ref document number: 602015049438

Country of ref document: DE

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: AT

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

Ref country code: DK

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

Ref country code: IT

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

Ref country code: ES

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

PLBE No opposition filed within time limit

Free format text: ORIGINAL CODE: 0009261

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: NO OPPOSITION FILED WITHIN TIME LIMIT

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: PL

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

26N No opposition filed

Effective date: 20210112

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: MC

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

REG Reference to a national code

Ref country code: CH

Ref legal event code: PL

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: SI

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

REG Reference to a national code

Ref country code: BE

Ref legal event code: MM

Effective date: 20200930

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: LU

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20200923

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: FR

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20200930

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: CH

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20200930

Ref country code: BE

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20200930

Ref country code: LI

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20200930

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: TR

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

Ref country code: MT

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

Ref country code: CY

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: MK

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

Ref country code: AL

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200325

P01 Opt-out of the competence of the unified patent court (upc) registered

Effective date: 20230530

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: NL

Payment date: 20250820

Year of fee payment: 11

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: DE

Payment date: 20250820

Year of fee payment: 11

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: GB

Payment date: 20250820

Year of fee payment: 11

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: IE

Payment date: 20250822

Year of fee payment: 11